WO1996028951A1 - Implant device with electrostatic discharge protection - Google Patents

Implant device with electrostatic discharge protection Download PDF

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Publication number
WO1996028951A1
WO1996028951A1 PCT/AU1995/000848 AU9500848W WO9628951A1 WO 1996028951 A1 WO1996028951 A1 WO 1996028951A1 AU 9500848 W AU9500848 W AU 9500848W WO 9628951 A1 WO9628951 A1 WO 9628951A1
Authority
WO
WIPO (PCT)
Prior art keywords
transmitter
receiver
signals
external
implantable
Prior art date
Application number
PCT/AU1995/000848
Other languages
French (fr)
Inventor
Kenneth Robert Dickson
David Kerry Money
Peter Scot Single
Original Assignee
Cochlear Limited
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Cochlear Limited filed Critical Cochlear Limited
Priority to EP95941544A priority Critical patent/EP0760196B1/en
Priority to DE69532116T priority patent/DE69532116D1/en
Priority to AU42934/96A priority patent/AU694831B2/en
Priority to JP8527100A priority patent/JPH10500607A/en
Publication of WO1996028951A1 publication Critical patent/WO1996028951A1/en

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/372—Arrangements in connection with the implantation of stimulators
    • A61N1/37211—Means for communicating with stimulators
    • A61N1/37217—Means for communicating with stimulators characterised by the communication link, e.g. acoustic or tactile
    • A61N1/37223—Circuits for electromagnetic coupling
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/36036—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation of the outer, middle or inner ear
    • A61N1/36038—Cochlear stimulation
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/50—Customised settings for obtaining desired overall acoustical characteristics
    • H04R25/505—Customised settings for obtaining desired overall acoustical characteristics using digital signal processing
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/362—Heart stimulators
    • A61N1/37—Monitoring; Protecting
    • A61N1/3718—Monitoring of or protection against external electromagnetic fields or currents
    • H—ELECTRICITY
    • H02—GENERATION; CONVERSION OR DISTRIBUTION OF ELECTRIC POWER
    • H02H—EMERGENCY PROTECTIVE CIRCUIT ARRANGEMENTS
    • H02H9/00—Emergency protective circuit arrangements for limiting excess current or voltage without disconnection
    • H02H9/04—Emergency protective circuit arrangements for limiting excess current or voltage without disconnection responsive to excess voltage
    • H02H9/041—Emergency protective circuit arrangements for limiting excess current or voltage without disconnection responsive to excess voltage using a short-circuiting device
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/60—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles
    • H04R25/604—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of acoustic or vibrational transducers
    • H04R25/606—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of acoustic or vibrational transducers acting directly on the eardrum, the ossicles or the skull, e.g. mastoid, tooth, maxillary or mandibular bone, or mechanically stimulating the cochlea, e.g. at the oval window

Definitions

  • This invention pertains to implantable de ⁇ vices used to provide various types of therapy, and more particularly, to such devices having protection means from high energy ambient electrical interference such as electrostatic discharge (ESD) .
  • ESD electrostatic discharge
  • Implantable electronic devices are used to provide therapy to patients suffering from a wide range of health problems. For example, cochlear de- •vices are used to aid people suffering acute loss of hearing. Pacemakers and cardioversion/defibrillation devices are used to aid patients with cardiac arrhyth- ias.
  • a further objective is to provide a system in which the protection means is completely passive so that it does not interfere with the normal operation of the device.
  • Yet another objective is to provide a protec ⁇ tive means which is relatively inexpensive and easy to implement to reduce the costs of a new design and/or retrofit.
  • Other objectives and advantages of the inven ⁇ tion shall become apparent from the following descrip ⁇ tion.
  • Implantable devices can be grouped into three categories.
  • the first category consists of devices which require substantially continuous communication between the implant and an external component.
  • Cochlear devices fall into this category since they require continuous signal transmission from a speech processor so that the patient can sense external sounds.
  • the second category consists of devices which normally operate independently, however, at regular or preset intervals they do exchange information with an external component to receive new or updated program- ming or to download information. Pacemakers and cardioversion/defibrillator devices fall into this second category.
  • the third category consists of devices which, after implantation, operate without any communication with the outside world. As shall be seen from the discussion below, the present invention is applicable primarily to devices of the first and second categories.
  • cochlear device refers to a device consisting of an external speech processor and an implant.
  • the external speech processor receives ambient sounds, converts the sounds into electrical signals and transmits these signals via a transmitter coil by electromagnetic induction to the implant.
  • the implant applies these signals to the auditory nerve of the patient.
  • ESD protection can be provided to the external speech processor to protect the internal im- plant.
  • a device constructed in accordance with this invention includes an internal portion for providing therapy, such as a cochlear implant, and an external portion, such as a speech processor.
  • the external portion is provided with a transmitter coil and the internal portion has a receiver coil arranged so that when the two coils are in close proximity, electrical signals are sent from the transmitter to the receiver coil.
  • the external device is provided with an ESD suppressing means for suppressing ESD pulses thereby insuring that they are not transmitted to the receiver coil.
  • the single Figure is a schematic diagram of a cochlear implant system incorporating the present invention.
  • a cochlear device .10 constructed in accordance with this invention includes an implantable or internal portion 12, which in this case is a cochlear implant, and an external portion, which in this case is a speech processor 14.
  • the speech processor includes a microphone _ , an encoder 1J3 and a transmitter 2.0. It should be understood that the transmitter .2C) has a number of elements of which only transmitter coil 22. is shown for the sake of clarity.
  • the cochlear implant ___ includes a receiver 24. Again, this receiver includes various elements, of which only the receiver coil ___ is shown.
  • Device 1.4 further includes a step-up transformer 2__, a tuning capacitor ,3_0, a power storage capacitor __2_, and a diode -
  • the device 12. further includes a data receiver circuit 3$., with a plurality of electrode output lines 38.
  • the system ) described so far is fairly conventional and operates as follows.
  • the cochlear implant __2 is implanted into a patient with the receiver coil 26, disposed subcutaneously near skin 40.
  • the external device 24, is disposed outside the body with the transmitter coil 2J2 positioned adjacent to the receiver coil 2_6 so that the skin 4JQ extends therebetween.
  • Device 12 is disposed in an insulated metal casing, which has been omitted in the figure.
  • Ambient sounds are picked up and converted into corresponding electrical signals by microphone 16. ' These signals are encoded by encoder .18.
  • the transmitter J2_0 receives the encoded signals and transmits them through the coils 2 , 23. to receiver 24.
  • the received signals are received by data re ⁇ DC circuit 1_6 and translated into impulses for the electrode outputs ___.
  • the wearer is trained so that he can recognize the sounds picked up by microphone 16 . through the corresponding signals appearing on electrodes 38.
  • Diode .34. is used to charge capacitor 3_2 which acts as a temporary power supply to provide power to the data receiver circuit 2£ and other components of the implant (not shown) .
  • ESD pulses can be picked up by portion l ⁇ and transmitted from coil 22 to coil 26. Since the energy content of these extremely short duration pulses is very high, they could damage vari ⁇ ous elements of the implant 12.
  • a protective device 4. is provided in the transmitter 20. This device is used to suppress the ESD pulses so that they do not propagate to the implant portion ____.
  • the protective device could consist of a pair of Zener diodes ⁇ 6 , ⁇ _j_ con ⁇ nected back-to-back, as shown.
  • Other ESD suppressing components are known which could be provided in the device 22. such as, for example, diodes connected from various internal inputs and outputs of device 12. to ground and/or the power supply (i.e., storage capac ⁇ itor __2.) '
  • diodes connected from various internal inputs and outputs of device 12. to ground and/or the power supply (i.e., storage capac ⁇ itor __2.)
  • such an implementation would take up precious space within the implant, increase the component count and consequently decrease the reliability of the device (a concern which is critical in an implanted device) .
  • devices already implanted could not be protected by the addition of these diodes, without being explanted and replaced.
  • the present invention in the external portion provides a much more effective solution. This arrangement is much easier to implement. Moreover, existing implanted devices could be easily retro ⁇ fitted, since only the external portion need be modi ⁇ fied.
  • the actual protection device 4_4 is standard in the art, and other transient suppressing mechanisms could be employed. What is unusual about the overall arrangement is that applying the mechanism to the transmitter protects the receiver.

Abstract

A protective component (44) is provided for protecting a cochlear implant (12) from external electrostatic discharges. The implant receives signals through a receiver coil (26) inductively coupled to a transmitter coil (22). The protective component (44) is disposed across the coil (22) of the transmitter (20).

Description

IMPLANT DEVICE WITH ELECTROSTATIC DISCHARGE PROTECTION
BACKGROUND OF INVENTION
A. Field of Invention
This invention pertains to implantable de¬ vices used to provide various types of therapy, and more particularly, to such devices having protection means from high energy ambient electrical interference such as electrostatic discharge (ESD) .
B. Description of the Prior Art
Implantable electronic devices are used to provide therapy to patients suffering from a wide range of health problems. For example, cochlear de- •vices are used to aid people suffering acute loss of hearing. Pacemakers and cardioversion/defibrillation devices are used to aid patients with cardiac arrhyth- ias.
Since these devices, when implanted, are immersed in fluids which are highly electrolytic and, since they are provided in an electrically conductive casing, one would expect that they would be well shielded from ambient electrical interference. In fact, a very large number of such devices have been implanted and in use for the last twenty years and the number of failures attributed to any ambient elec¬ trical interference has been minimal. However, there has been a small number of instances known to the inventors where cochlear implants have failed, appar¬ ently due to high energy level ambient electromagnetic fields.
Thus, it appears that there is a need for improving the protection of implantable devices from ambient electromagnetic interference. Moreover, since a large number of such devices have already been im¬ planted, it would be .beneficial to have a means of increasing the protection of the implanted devices in a manner which does not require explantation.
OBJECTIVES AND SUMMARY OF THE INVENTION
In view of the above, it is an objective of the present invention to provide an implant system with protection means against ambient electromagnetic interference, said protection means being disposed outside the implanted device.
A further objective is to provide a system in which the protection means is completely passive so that it does not interfere with the normal operation of the device.
Yet another objective is to provide a protec¬ tive means which is relatively inexpensive and easy to implement to reduce the costs of a new design and/or retrofit. Other objectives and advantages of the inven¬ tion shall become apparent from the following descrip¬ tion.
Implantable devices can be grouped into three categories. The first category consists of devices which require substantially continuous communication between the implant and an external component. Cochlear devices fall into this category since they require continuous signal transmission from a speech processor so that the patient can sense external sounds.
The second category consists of devices which normally operate independently, however, at regular or preset intervals they do exchange information with an external component to receive new or updated program- ming or to download information. Pacemakers and cardioversion/defibrillator devices fall into this second category.
The third category consists of devices which, after implantation, operate without any communication with the outside world. As shall be seen from the discussion below, the present invention is applicable primarily to devices of the first and second categories.
The term "cochlear device" as used in this application refers to a device consisting of an external speech processor and an implant. The external speech processor receives ambient sounds, converts the sounds into electrical signals and transmits these signals via a transmitter coil by electromagnetic induction to the implant. The implant applies these signals to the auditory nerve of the patient.
As previously mentioned, the problem addressed by this invention arose with cochlear devices. More particularly, a small number of cochlear devices failed and, on explantation, it was found that several of the elements associated with the data receiving function were damaged by a high level electrical shock. A number of experiments were performed in a laboratory to try to induce similar failures in other cochlear devices. More particularly, implants were submersed in a saline solution simulating body fluids and tissues, and subjected to high level electromagnetic fields so as to produce electrostatic discharge (ESD) into the implant. ESD was the primary suspect for causing the failures because one failure was reported after the patient (a child) used a slide in a playground and the inventors noted that on very dry days children using slides became electrostatically charged to about 15 KVDC.
In one experiment, electrical shocks were applied to the surface of the saline solution. As expected, the saline solution attenuated the shocks and protected the implant from damage.
In another experiment, electrical conductors were connected to the metal casing of the implant and electrical shocks were applied to the conductors. These shocks did damage some of the elements of the implant, but not in a manner that matched the damage found in the failed devices.
Surprisingly, it was discovered, however, that the mode of failure was replicated exactly when the transmitter coil of a speech processor was placed adjacent to the implant and ESD pulses were applied to the conductors connected to the transmitter coil. Thus, the present inventors have discovered that electrostatic discharge to the transmitter coil of the external speech processor was transmitted by electro- magnetic coupling to the implant where its high in¬ tensity and energy contents damaged the implant's receiver elements. Importantly, ESD protection, according to this invention, can be provided to the external speech processor to protect the internal im- plant.
A device constructed in accordance with this invention includes an internal portion for providing therapy, such as a cochlear implant, and an external portion, such as a speech processor. The external portion is provided with a transmitter coil and the internal portion has a receiver coil arranged so that when the two coils are in close proximity, electrical signals are sent from the transmitter to the receiver coil. Importantly, the external device is provided with an ESD suppressing means for suppressing ESD pulses thereby insuring that they are not transmitted to the receiver coil.
BRIEF DESCRIPTION OF TEE DRAWING
The single Figure is a schematic diagram of a cochlear implant system incorporating the present invention.
DETAILED DESCRIPTION OF THE INVENTION
Referring now to the single figure, a cochlear device .10 constructed in accordance with this invention includes an implantable or internal portion 12, which in this case is a cochlear implant, and an external portion, which in this case is a speech processor 14.. The speech processor includes a microphone _ , an encoder 1J3 and a transmitter 2.0. It should be understood that the transmitter .2C) has a number of elements of which only transmitter coil 22. is shown for the sake of clarity.
The cochlear implant ___ includes a receiver 24. Again, this receiver includes various elements, of which only the receiver coil ___ is shown. Device 1.4 further includes a step-up transformer 2__, a tuning capacitor ,3_0, a power storage capacitor __2_, and a diode - The device 12. further includes a data receiver circuit 3$., with a plurality of electrode output lines 38. The system ) described so far is fairly conventional and operates as follows.
The cochlear implant __2 is implanted into a patient with the receiver coil 26, disposed subcutaneously near skin 40. The external device 24, is disposed outside the body with the transmitter coil 2J2 positioned adjacent to the receiver coil 2_6 so that the skin 4JQ extends therebetween.
With the exception of receiver 2J>, Device 12 is disposed in an insulated metal casing, which has been omitted in the figure.
Ambient sounds are picked up and converted into corresponding electrical signals by microphone 16.' These signals are encoded by encoder .18. The transmitter J2_0 receives the encoded signals and transmits them through the coils 2 , 23. to receiver 24. The received signals are received by data re¬ ceiver circuit 1_6 and translated into impulses for the electrode outputs ___. The wearer is trained so that he can recognize the sounds picked up by microphone 16. through the corresponding signals appearing on electrodes 38.
Diode .34. is used to charge capacitor 3_2 which acts as a temporary power supply to provide power to the data receiver circuit 2£ and other components of the implant (not shown) .
When the coils __2 , 2__ are disposed in the opposing relation shown in the figure, they are coupled electromagnetically by the mutual inductance 49 between the coils. In addition, a leakage path exists across the skin 4J3 between the coils 2 , 26, represented symbolically in the figure by a series capacitor-resistor combination 42.. However, this path does not play a part in the normal operation of the system.
As previously described, the present invent¬ ors have discovered that ESD pulses can be picked up by portion l± and transmitted from coil 22 to coil 26. Since the energy content of these extremely short duration pulses is very high, they could damage vari¬ ous elements of the implant 12.
In order to prevent this damage, a protective device 4. is provided in the transmitter 20. This device is used to suppress the ESD pulses so that they do not propagate to the implant portion ____. For
SUBSTTTUTΈSHEET(Rule26) example, as shown in the figure, the protective device could consist of a pair of Zener diodes ±6 , <_j_ con¬ nected back-to-back, as shown. Other ESD suppressing components are known which could be provided in the device 22. such as, for example, diodes connected from various internal inputs and outputs of device 12. to ground and/or the power supply (i.e., storage capac¬ itor __2.) ' However, such an implementation would take up precious space within the implant, increase the component count and consequently decrease the reliability of the device (a concern which is critical in an implanted device) . Moreover, devices already implanted could not be protected by the addition of these diodes, without being explanted and replaced.
The present invention in the external portion provides a much more effective solution. This arrangement is much easier to implement. Moreover, existing implanted devices could be easily retro¬ fitted, since only the external portion need be modi¬ fied. The actual protection device 4_4 is standard in the art, and other transient suppressing mechanisms could be employed. What is unusual about the overall arrangement is that applying the mechanism to the transmitter protects the receiver.
Although the invention has been described with reference to a preferred embodiment, it is to be understood that this embodiment is merely illustrative of the application of the principles of the invention. Accordingly, the embodiment described in particular should be considered exemplary, not limiting, with respect to the following claims.

Claims

We Claim:
1. A device for providing therapy to a patient comprising: an implantable portion for implantation in the patient, said implantable portion including a receiver for receiving signals; an external portion for generating signals, said external portion including a transmitter for transmitting signals to said receiver when said external portion is positioned to provide inductive coupling between said transmitter and said receiver; and a protective device coupled to said transmitter provided to suppress the effect of electrostatic discharge to prevent propagation of said discharge energy to said implantable portion.
2. The device of claim 1 wherein said implantable portion is a cochlear implant.
3. The device of claim 2 wherein said external device is a speech encoder.
4. The device of claim 1 wherein said receiver and transmitter include respective coils.
5. The device of claim 4 wherein said protective device is disposed in said transmitter.
6. The device of claim 5 wherein said protective device is electrically connected across said transmitter coil.
7. A device for providing therapy to a patient, comprising: an implantable portion for implantation in a patient, said implantable portion including- a receiver for receiving electrical signals; and an external portion for generating said electrical signals, said external portion including a transmitter adapted to transmit said signals to said receiver by magnetic induction when said transmitter is positioned adjacent to said receiver; said external portion further including a protective device arranged to suppress undesirable transient signals from propagating from said transmitter to said receiver.
8. The system of claim 7 wherein said transmitter and said receiver each include a coil, said coils being inductively coupled when said transmitter is positioned adjacent to said receiver.
9. The system of claim 8 wherein said protective portion is electrically coupled across said transmitter coil.
10. The system of claim 8 wherein said protective device is selected to suppress the damaging effects of electrostatic discharges.
11. The system of claim 10 wherein said implantable portion is a cochlear implant and said external portion is a speech processor.
12. A method of protecting a therapeutic device from electrostatic discharges, said device including an implantable portion having a receiver for receiving signals related to therapy, and an external portion generating said signals and including a transmitter for inductive transmission of said signals to said receiver when said transmitter and receiver are adjacent, said method comprising suppressing undesirable electromagnetic interference in said transmitter to prevent said interference from damaging said implantable portion.
13. The method of claim 12 wherein said suppressing is performed by a protective device disposed in said transmitter for suppressing electrostatic discharges.
PCT/AU1995/000848 1995-03-09 1995-12-14 Implant device with electrostatic discharge protection WO1996028951A1 (en)

Priority Applications (4)

Application Number Priority Date Filing Date Title
EP95941544A EP0760196B1 (en) 1995-03-09 1995-12-14 Implant device with electrostatic discharge protection
DE69532116T DE69532116D1 (en) 1995-03-09 1995-12-14 IMPLANT DEVICE WITH PROTECTION AGAINST ELECTROSTATIC DISCHARGE
AU42934/96A AU694831B2 (en) 1995-03-09 1995-12-14 Implant device with electrostatic discharge protection
JP8527100A JPH10500607A (en) 1995-03-09 1995-12-14 Implantation device with electrostatic discharge protection

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US08/401,468 US5584870A (en) 1995-03-09 1995-03-09 Implant ESD protection network
US08/401,468 1995-03-09

Publications (1)

Publication Number Publication Date
WO1996028951A1 true WO1996028951A1 (en) 1996-09-19

Family

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Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/AU1995/000848 WO1996028951A1 (en) 1995-03-09 1995-12-14 Implant device with electrostatic discharge protection

Country Status (7)

Country Link
US (1) US5584870A (en)
EP (1) EP0760196B1 (en)
JP (1) JPH10500607A (en)
AU (1) AU694831B2 (en)
CA (1) CA2189742A1 (en)
DE (1) DE69532116D1 (en)
WO (1) WO1996028951A1 (en)

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* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US7708912B2 (en) 2008-06-16 2010-05-04 Polytronics Technology Corporation Variable impedance composition
US8989840B2 (en) 2004-03-30 2015-03-24 Medtronic, Inc. Lead electrode for use in an MRI-safe implantable medical device
US9044593B2 (en) 2007-02-14 2015-06-02 Medtronic, Inc. Discontinuous conductive filler polymer-matrix composites for electromagnetic shielding
US9155877B2 (en) 2004-03-30 2015-10-13 Medtronic, Inc. Lead electrode for use in an MRI-safe implantable medical device
US9186499B2 (en) 2009-04-30 2015-11-17 Medtronic, Inc. Grounding of a shield within an implantable medical lead
US9259572B2 (en) 2007-04-25 2016-02-16 Medtronic, Inc. Lead or lead extension having a conductive body and conductive body contact
US9302101B2 (en) 2004-03-30 2016-04-05 Medtronic, Inc. MRI-safe implantable lead
US9463317B2 (en) 2012-04-19 2016-10-11 Medtronic, Inc. Paired medical lead bodies with braided conductive shields having different physical parameter values
US9731119B2 (en) 2008-03-12 2017-08-15 Medtronic, Inc. System and method for implantable medical device lead shielding
US9993638B2 (en) 2013-12-14 2018-06-12 Medtronic, Inc. Devices, systems and methods to reduce coupling of a shield and a conductor within an implantable medical lead
US10084250B2 (en) 2005-02-01 2018-09-25 Medtronic, Inc. Extensible implantable medical lead
US10155111B2 (en) 2014-07-24 2018-12-18 Medtronic, Inc. Methods of shielding implantable medical leads and implantable medical lead extensions
US10279171B2 (en) 2014-07-23 2019-05-07 Medtronic, Inc. Methods of shielding implantable medical leads and implantable medical lead extensions
US10537730B2 (en) 2007-02-14 2020-01-21 Medtronic, Inc. Continuous conductive materials for electromagnetic shielding

Families Citing this family (31)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5728154A (en) * 1996-02-29 1998-03-17 Minnesota Mining And Manfacturing Company Communication method for implantable medical device
US6198972B1 (en) * 1997-04-30 2001-03-06 Medtronic, Inc. Control of externally induced current in implantable medical devices
US6330464B1 (en) 1998-08-26 2001-12-11 Sensors For Medicine & Science Optical-based sensing devices
US6597227B1 (en) * 2000-01-21 2003-07-22 Atheros Communications, Inc. System for providing electrostatic discharge protection for high-speed integrated circuits
US6624998B2 (en) 2000-01-24 2003-09-23 Medtronic, Inc. Electrostatic discharge protection scheme in low potential drop environments
EP1294329A4 (en) * 2000-04-20 2004-03-31 Cochlear Ltd Transcutaneous power optimization circuit for cochlear implant
US6451055B1 (en) 2000-04-25 2002-09-17 The Penn State Research Foundation Artificial heart data communication system
US6458164B1 (en) 2000-04-25 2002-10-01 The Penn State Research Foundation Artificial heart with energy recovery
US6579315B1 (en) 2000-04-25 2003-06-17 The Penn State Research Foundation Artificial heart power supply system
US6395027B1 (en) 2000-04-25 2002-05-28 The Penn State Research Foundation Artificial heart with arrhythmia signalling
US6478820B1 (en) 2000-04-25 2002-11-12 The Penn State Research Foundation Artificial heart with synchronous rectification
US7553280B2 (en) 2000-06-29 2009-06-30 Sensors For Medicine And Science, Inc. Implanted sensor processing system and method
US8600519B2 (en) * 2001-04-13 2013-12-03 Greatbatch Ltd. Transient voltage/current protection system for electronic circuits associated with implanted leads
CA2445127C (en) * 2001-05-04 2011-12-13 Sensors For Medicine And Science, Inc. Electro-optical sensing device with reference channel
EP1620714B1 (en) * 2003-04-15 2014-03-12 Senseonics, Incorporated System and method for attenuating the effect of ambient light on an optical sensor
US7242981B2 (en) * 2003-06-30 2007-07-10 Codman Neuro Sciences Sárl System and method for controlling an implantable medical device subject to magnetic field or radio frequency exposure
US7647097B2 (en) * 2003-12-29 2010-01-12 Braingate Co., Llc Transcutaneous implant
US7877150B2 (en) 2004-03-30 2011-01-25 Medtronic, Inc. Lead electrode for use in an MRI-safe implantable medical device
US7844343B2 (en) 2004-03-30 2010-11-30 Medtronic, Inc. MRI-safe implantable medical device
US7794499B2 (en) 2004-06-08 2010-09-14 Theken Disc, L.L.C. Prosthetic intervertebral spinal disc with integral microprocessor
US8897884B2 (en) * 2004-11-26 2014-11-25 St. Jude Medical Ab Implantable medical device with a voltage protection circuit
US7308292B2 (en) 2005-04-15 2007-12-11 Sensors For Medicine And Science, Inc. Optical-based sensing devices
US8027736B2 (en) 2005-04-29 2011-09-27 Medtronic, Inc. Lead electrode for use in an MRI-safe implantable medical device
US7853332B2 (en) 2005-04-29 2010-12-14 Medtronic, Inc. Lead electrode for use in an MRI-safe implantable medical device
WO2007087875A1 (en) * 2006-01-13 2007-08-09 Universität Duisburg-Essen Stimulation system, in particular a cardiac pacemaker
US20110043217A1 (en) * 2008-01-02 2011-02-24 Kostas Ioannis Tsampazis Electrode fault detection
DE102015112098A1 (en) 2014-07-25 2016-01-28 Minnetronix, Inc. Coil parameters and control
US9855376B2 (en) 2014-07-25 2018-01-02 Minnetronix, Inc. Power scaling
DE102016100476A1 (en) 2015-01-14 2016-07-14 Minnetronix, Inc. Decentralized transformer
DE102016100534A1 (en) 2015-01-16 2016-07-21 Vlad BLUVSHTEIN Data transmission in a transcutaneous energy transmission system
US10193395B2 (en) 2015-04-14 2019-01-29 Minnetronix, Inc. Repeater resonator

Citations (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
GB2016276A (en) * 1978-01-21 1979-09-26 Ross Foundation For Research I Sensory system
US4223679A (en) * 1979-02-28 1980-09-23 Pacesetter Systems, Inc. Telemetry means for tissue stimulator system
EP0124930A1 (en) * 1983-04-11 1984-11-14 The Commonwealth Of Australia Cochlear implant system for an auditory prosthesis
EP0145419A2 (en) * 1983-12-09 1985-06-19 Minnesota Mining And Manufacturing Company Direct current blocking circuit and implantable device using same
EP0529949A2 (en) * 1991-08-27 1993-03-03 AT&T Corp. Common mode voltage surge protection circuitry
US5217011A (en) * 1989-06-20 1993-06-08 Storz Instrument Company Method and apparatus for transdermal communication
US5314457A (en) * 1993-04-08 1994-05-24 Jeutter Dean C Regenerative electrical

Family Cites Families (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3751605A (en) * 1972-02-04 1973-08-07 Beckman Instruments Inc Method for inducing hearing
US3920025A (en) * 1974-07-15 1975-11-18 Medtronic Inc Electro-medical stimulator system
CA1189147A (en) * 1980-12-12 1985-06-18 James F. Patrick Speech processors
EP0200321A3 (en) * 1985-03-20 1987-03-11 Ingeborg J. Hochmair Transcutaneous signal transmission system
US4592359A (en) * 1985-04-02 1986-06-03 The Board Of Trustees Of The Leland Stanford Junior University Multi-channel implantable neural stimulator
DE3821970C1 (en) * 1988-06-29 1989-12-14 Ernst-Ludwig Von Dr. 8137 Berg De Wallenberg-Pachaly
US5095904A (en) * 1989-09-08 1992-03-17 Cochlear Pty. Ltd. Multi-peak speech procession
US5197468A (en) * 1990-02-13 1993-03-30 Proctor Paul W Device for protecting an electronic prosthesis from adverse effects of RF and/or electrostatic energy

Patent Citations (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
GB2016276A (en) * 1978-01-21 1979-09-26 Ross Foundation For Research I Sensory system
US4223679A (en) * 1979-02-28 1980-09-23 Pacesetter Systems, Inc. Telemetry means for tissue stimulator system
EP0124930A1 (en) * 1983-04-11 1984-11-14 The Commonwealth Of Australia Cochlear implant system for an auditory prosthesis
EP0247649A1 (en) * 1983-04-11 1987-12-02 The Commonwealth Of Australia Cochlear implant prosthesis current switching and power supply
EP0145419A2 (en) * 1983-12-09 1985-06-19 Minnesota Mining And Manufacturing Company Direct current blocking circuit and implantable device using same
US5217011A (en) * 1989-06-20 1993-06-08 Storz Instrument Company Method and apparatus for transdermal communication
EP0529949A2 (en) * 1991-08-27 1993-03-03 AT&T Corp. Common mode voltage surge protection circuitry
US5314457A (en) * 1993-04-08 1994-05-24 Jeutter Dean C Regenerative electrical

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
See also references of EP0760196A4 *

Cited By (23)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US9302101B2 (en) 2004-03-30 2016-04-05 Medtronic, Inc. MRI-safe implantable lead
US8989840B2 (en) 2004-03-30 2015-03-24 Medtronic, Inc. Lead electrode for use in an MRI-safe implantable medical device
US9155877B2 (en) 2004-03-30 2015-10-13 Medtronic, Inc. Lead electrode for use in an MRI-safe implantable medical device
US10084250B2 (en) 2005-02-01 2018-09-25 Medtronic, Inc. Extensible implantable medical lead
US9044593B2 (en) 2007-02-14 2015-06-02 Medtronic, Inc. Discontinuous conductive filler polymer-matrix composites for electromagnetic shielding
US10537730B2 (en) 2007-02-14 2020-01-21 Medtronic, Inc. Continuous conductive materials for electromagnetic shielding
US10398893B2 (en) 2007-02-14 2019-09-03 Medtronic, Inc. Discontinuous conductive filler polymer-matrix composites for electromagnetic shielding
US9259572B2 (en) 2007-04-25 2016-02-16 Medtronic, Inc. Lead or lead extension having a conductive body and conductive body contact
US9731119B2 (en) 2008-03-12 2017-08-15 Medtronic, Inc. System and method for implantable medical device lead shielding
US7708912B2 (en) 2008-06-16 2010-05-04 Polytronics Technology Corporation Variable impedance composition
US9205253B2 (en) 2009-04-30 2015-12-08 Medtronic, Inc. Shielding an implantable medical lead
US9452284B2 (en) 2009-04-30 2016-09-27 Medtronic, Inc. Termination of a shield within an implantable medical lead
US9629998B2 (en) 2009-04-30 2017-04-25 Medtronics, Inc. Establishing continuity between a shield within an implantable medical lead and a shield within an implantable lead extension
US9272136B2 (en) 2009-04-30 2016-03-01 Medtronic, Inc. Grounding of a shield within an implantable medical lead
US10035014B2 (en) 2009-04-30 2018-07-31 Medtronic, Inc. Steering an implantable medical lead via a rotational coupling to a stylet
US9220893B2 (en) 2009-04-30 2015-12-29 Medtronic, Inc. Shielded implantable medical lead with reduced torsional stiffness
US10086194B2 (en) 2009-04-30 2018-10-02 Medtronic, Inc. Termination of a shield within an implantable medical lead
US9216286B2 (en) 2009-04-30 2015-12-22 Medtronic, Inc. Shielded implantable medical lead with guarded termination
US9186499B2 (en) 2009-04-30 2015-11-17 Medtronic, Inc. Grounding of a shield within an implantable medical lead
US9463317B2 (en) 2012-04-19 2016-10-11 Medtronic, Inc. Paired medical lead bodies with braided conductive shields having different physical parameter values
US9993638B2 (en) 2013-12-14 2018-06-12 Medtronic, Inc. Devices, systems and methods to reduce coupling of a shield and a conductor within an implantable medical lead
US10279171B2 (en) 2014-07-23 2019-05-07 Medtronic, Inc. Methods of shielding implantable medical leads and implantable medical lead extensions
US10155111B2 (en) 2014-07-24 2018-12-18 Medtronic, Inc. Methods of shielding implantable medical leads and implantable medical lead extensions

Also Published As

Publication number Publication date
EP0760196B1 (en) 2003-11-12
CA2189742A1 (en) 1996-09-19
JPH10500607A (en) 1998-01-20
US5584870A (en) 1996-12-17
AU694831B2 (en) 1998-07-30
AU4293496A (en) 1996-10-02
DE69532116D1 (en) 2003-12-18
EP0760196A1 (en) 1997-03-05
EP0760196A4 (en) 1998-02-11

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